Collagen sponge

ABSTRACT

A resilient resorbable chemically crosslinked collagen sponge for promoting soft tissue volume augmentation in the oral region, comprising 60-96% (w/w) collagen and 4-40% (w/w) elastin, which shows by mercury intrusion porosimetry interconnected pores with a median pore diameter between 50 and 90 μm and at least 80% porosity with a pore diameter more than 10 μm, an onset temperature of 45 to 57° C. and a density in dry state from 50 to 65 mg/cm 3 . A process for preparing a resilient resorbable chemically crosslinked collagen sponge. A method of using a resilient resorbable chemically crosslinked collagen sponge as an implant in the oral cavity for soft tissue volume augmentation.

This application claims the benefit of European Patent Application No.14197987.2 filed on Dec. 15, 2014, the disclosure of which isincorporated by reference in its entirety.

FIELD OF THE INVENTION

The invention relates to a new resilient resorbable chemicallycrosslinked collagen sponge for promoting soft tissue volumeaugmentation in the oral region, a process for preparing that resilientresorbable chemically crosslinked collagen sponge and the use thereof asan implant in the oral cavity for soft tissue volume augmentation.

BACKGROUND OF THE INVENTION

Soft tissue volume augmentation has become one of the major challengesin dental and cranio-maxillofacial surgery. In order to improve bothfunctional and esthetic outcomes by soft tissue volume augmentation,autogenous tissue grafts such as the free gingival graft (FGG) or thesubepithelial connective tissue graft (SCTG), despite their drawbacksare still broadly used for various indications and considered to be thegold standard (F. Cairo et al., 2008, J. Clin. Periodontol. 35 (Suppl.8), 314-319; R. Jung et al., 2004, Int. J. Periodontics RestorativeDent. 24(6), 545-553 and D. Thoma, 2009, Clin. Oral Implants Res. 20(suppl. 4), 146-165). However, the harvesting procedure for autogenoustissue at a second surgical site usually in the palate has drawbacks forthe patient and limitations as to the quality and quantity of tissuethat can be retrieved.

A regenerative device for promoting soft tissue volume augmentation inthe oral region is thus desirable.

Gingival cells of the oral connective tissue are exposed to complexmechanical forces during mastication, swallowing, tongue movement,speech, tooth movement and orthodontic treatment. Especially duringwound healing following surgical procedures, internal and externalforces may occur, creating pressure upon the regenerative device andnewly formed tissue.

A regenerative device has to meet certain criteria before being used inthe oral cavity for soft tissue volume augmentation: It must bebiocompatible, resorbable in vivo, allow gingival ingrowth, show a goodlevel of tissue integration such as to allow uneventful healing (withoutexcessive inflammation or dehiscence) and be able to withstandmechanical forces by acting as a scaffold that maintains tissue volumeduring a sufficient time during the wound healing process afterimplantation, generally at least about 3 months.

No such regenerative device has so far been disclosed in the prior art.

H. Mathes et al. in “A Bioreactor Test System to mimic the Biologicaland Mechanical Environment of Oral Soft Tissues and to EvaluateSubstitutes for Connective Tissue Gaffs”, 2010, Biotechnology andBioengineering, Vol. 9999, No. 9999, disclose that such properties of aregenerative device consisting of a collagen sponge might be achieved bystiffening the matrix body by crosslinking of the collagen fibers to adegree allowing the right balance between mechanical stability (highdegree of crosslinking) and uneventful soft tissue healing (low degreeof crosslinking), but are totally silent on how to prepare such acollagen sponge. They disclose that three different collagen spongeprototypes consisting of porcine collagen type I and Ill with an averagepore diameter of 92 μm and 93% porosity and differing in their degree ofcrosslinking (prototypes provided by Geistlich Pharma, Wolhusen,Switzerland) showed after culture under mechanical stimulation for 14days a satisfying volume retention with a good fibroblast cell vitality.

DS Thoma et al. in “Soft tissue volume augmentation by the use ofcollagen-based matrixes: a volumetric analysis”, 2010, J. of Clin.Periodontology 37, 659-666, and “Soft tissue volume augmentation by theuse of collagen-based matrixes in a dog mandible—a histologicalanalysis”, 2011, J. Clin. Periodontol.: 38:1063-1070, disclose that oneof the collagen sponge prototypes referred to in the above publicationof H. Mathes et al. showed after a period of 28 or 84 days ofimplementation into a chronic ridge defect of a dog mandible the samevolume retention as the gold standard, SCTG (subendopithelial connectivetissue graft).

The prior art does not disclose or suggest what are the features of sucha chemically crosslinked collagen sponge prototype, or of any otherregenerative collagen device fulfilling the criteria set forth above fora use in the oral cavity for soft tissue volume augmentation, or howsuch a device can be prepared.

EP-1561480 discloses a resorbable collagen device for use as a duralsubstitute for growing meningeal tissue, comprising a chemicallycrosslinked collagen sheet which has a majority of pores below 10 μm anda method for preparing that collagen device comprising the steps ofmixing collagen with water under such conditions that the mixturecontains substantially solubilized collagen, lyophilizing the mixtureinto a collagen device and chemically crosslinking the collagen device,using as crosslinking agent formaldehyde or gluteraldehyde. A duralsubstitute is not, like a regenerative device for promoting soft tissuevolume augmentation in the oral region, exposed during wound healing topressure created by the above mentioned complex mechanical forces.

US-2004-0265785 describes a process for producing a collagen-elastinmembrane containing at least 20% (w/w) elastin, comprising the steps offirst chemically removing hydrophobic accompanying substances from anelastin containing collagen material of natural origin, then chemicallyremoving non-hydrophobic substances. The collagen-elastin product is notchemically crosslinked.

Boekema B. K. L. H. et al., 2014, Journal of Material Sciences:Materials in Medicine, Feb. 2014 25: 423-433, describe the effect onwound healing of pore size and crosslinking on collagen-elastinscaffolds used as dermal substitutes. The disclosed EDC-NHS chemicallycrosslinked scaffolds contain 10-15% elastin, have a pore size of 80 to120 μm and a denaturation temperature of 64 to 69° C. (see Table 1, page425). They are sterilized by ethylene oxide gas treatment. The authorsconclude that crosslinking negatively affects wound healing on severalimportant parameters, notably by reducing the ability of fibroblasts toproliferate and replace the dermal substitute by new tissue. A dermalsubstitute is not, like a regenerative device for promoting soft tissuevolume augmentation in the oral region, exposed during wound healing topressure created by the above mentioned complex mechanical forces.

The problem or objective of the invention is to find a regenerativecollagen device for promoting soft tissue volume augmentation in theoral region that is biocompatible, resorbable in vivo, allows gingivalingrowth, shows a good level of tissue integration such as to allowuneventful healing (without excessive inflammation or dehiscence) and beable to withstand mechanical forces by acting as a scaffold thatmaintains tissue volume during a sufficient time during the woundhealing process after implantation, generally at least about 3 months.

The above problem is solved by the invention as defined in the appendedclaims.

BRIEF SUMMARY OF THE INVENTION

The invention relates to a resilient resorbable chemically crosslinkedcollagen sponge for promoting soft tissue volume augmentation in theoral region, comprising 60-96% (w/w) collagen and 4-40% (w/w) elastin,which shows by mercury intrusion porosimetry interconnected pores with amedian pore diameter between 50 and 90 μm and at least 80% porosity witha pore diameter more than 10 μm, an onset temperature of 45 to 57° C.and a density in dry state from 50 to 65 mg/cm³.

The chemically crosslinked collagen sponge comprises 60-96% (w/w)collagen and 4-40% (w/w) elastin. The elastin content is here measuredby desmosine/iodesmosine determination according to a modification of aknown method involving hydrolysis and RP-HPLC (see e.g. Guida E. et al.1990 Development and validation of a high performance chromatographymethod for the determination of desmosines in tissues in Journal ofChromatography or Rodriguqe P 2008 Quantification of Mouse Lung ElastinDuring Prenatal Development in The Open Respiratory Medicine Journal).To determine the desmosine/isodesmosine content of dry elastin, theelastin of the sponge is subjected to elastin isolation procedures asdescribed by Starcher and Galione 1976 Purification and Comparison ofElastin from Different Animal Species in Analytical Biochemistry.

That sponge is suitably derived from tissues of natural origin whichcontain such proportions of collagen and elastin. Examples of suchtissues include mammalian (e.g. porcine or bovine) peritoneum orpericardium membrane, placenta membrane, small intestine submucosa (SIS)and dermis. Usually the collagen is predominantly collagen type I,collagen type III or a mixture thereof. The collagen may also include aproportion of notably collagen type II, type IV, type VI or type VIII orany combination of those or any collagen types.

BRIEF DESCRIPTION OF THE SEVERAL VIEWS OF THE DRAWING

The FIGURE shows the typical result of a cyclic compression test.

DETAILED DESCRIPTION OF THE INVENTION

The term “collagen” used in this application usually refers to thatcombination of 60-96% (w/w) collagen and 4-40% (w/w) elastin.

Preferably the chemically crosslinked collagen sponge comprises 70-90%(w/w) collagen and 10-30% (w/w) elastin.

An example of a suitable starting material for preparing such achemically crosslinked collagen sponge is a slurry of collagen fibresfrom the membrane prepared from porcine or bovine peritoneum by aprocess similar to that described in “Example” of EP-B1-1676592 or fromthe membrane Geistlich Bio-Gide® (obtainable from Geistlich Pharma A.G.,Switzerland) prepared from porcine peritoneum by a very similar processand/or a slurry of collagen fibres prepared from porcine dermis by aprocess similar to that described in Example 7 of WO 2012/084214.

The above resilient resorbable chemically crosslinked collagen spongepromotes soft tissue augmentation in the oral region by fosteringingrowth of gingival cells while keeping volume after loading andunloading of mechanical stresses.

For fostering ingrowth of gingival cells the chemically crosslinkedcollagen sponge must have a high porosity (pore volume fraction) in anappropriate diameter range for gingival fibroblasts to grow. It has beenfound that this ingrowth is suitably fostered when the sponge shows bymercury intrusion porosimetry interconnected pores with a median porediameter between 50 and 90 μm and at least 80%, preferably at least 90%,porosity with a pore diameter more than 10 μm. The chemicallycrosslinked sponge with such a distribution of pores is suitablyprepared by a process comprising mixing before crosslinking inappropriate proportions a slurry of collagen fibres from the membraneprepared from porcine or bovine peritoneum as disclosed in the previousparagraph and a slurry of collagen fibres prepared from porcine dermisas disclosed in the previous paragraph.

The term “resilient” here means that the chemically crosslinked collagensponge is resistant to pressure, i.e. capable of regaining a large partof its original volume after being submitted to pressure in vitro or invivo.

For keeping volume in the oral region the resilient resorbablechemically crosslinked sponge must be able to withstand the complexmechanical forces induced by mastication, tongue movement, speech andtooth movement by acting as a scaffold that maintains tissue volumeduring a sufficient time during the healing process after implantation,generally about 3 months. It has been found that this in vivo resilientbehaviour of the implant is attained when, in an in vitro mechanicaltest of cyclic compression at a temperature of 37° C. of the collagensponge wetted by a phosphate buffer saline (PBS) solution designed tomimic the body fluids, the thickness retention in respect to the initialthickness is at least 70%, preferably at least 80%, more preferably atleast 85%, or the hysteresis retention in respect of the first loadingis less than 55%, preferably less than 45%, after 49 cycles ofcompression to a pressure of 12.1 kPa.

It has been found that the above in vitro thickness retention of atleast 70% and hysteresis retention of less than 55% combined with invivo healing without excessive inflammation or dehiscence is attainedwhen the sponge shows an onset temperature from 45 to 57° C. and adensity in dry state from 50 to 65 mg/cm³.

The onset temperature is measured by DSC on the collagen sponge wettedwith a buffer solution according to US Pharmacopia standard: Ph. Eur.2.2.34, USP <891> (buffer composition for 1 litre of water: 8 g sodiumchloride, 0.2 g potassium phosphate, 1.15 g sodium phosphate and 0.2 gpotassium chloride; start temperature 15° C., end temperature 90° C.,heating rate 5° C./min). This parameter reflects the crosslinking degreeof the sponge. The onset temperature is closely linked to the sponge invitro resistance to cyclic compression (thickness retention orhysteresis retention in the mechanical test of cyclic compression), invivo resilience (keeping of tissue volume during a sufficient timeduring the healing process after implantation) and good integration intothe surrounding tissues (no excessive inflammation or dehiscence).

The required in vitro resistance to cyclic compression and the in vivoresilience combined with in vivo healing without without excessiveinflammation or dehiscence can be attained when the onset temperature isfrom 45 to 57° C., preferably from 46 to 53° C. When the onsettemperature is below 46° C., the in vitro resistance to cycliccompression and the in vivo resilience may not be sufficient. When theonset temperature is above 57° C., there is a substantial risk ofadverse events such as excessive inflammation and/or dehiscenceappearing after implantation.

The density in dry state, measured by weighing and measuring the volumeof the collagen sponge after extensive lyophilisation (as described indetail below), is another essential or critical parameter for reachingthe required in vitro resistance to cyclic compression and the in vivoresilience combined with in vivo healing without without excessiveinflammation or dehiscence. Those features can be attained when thedensity in dry state is from 50 to 65, preferably from 50 to 60 mg/cm³.When the density in dry state is below 50 mg/cm³, the in vitroresistance to cyclic compression and the in vivo resilience may not besufficient. When the density in dry state is above 65 mg/cm³, there is arisk of adverse events such as excessive inflammation and/or dehiscenceappearing after implantation.

The term “resorbable” here means that the chemically crosslinkedcollagen sponge is capable of being resorbed in vivo notably through theaction of collagenases and elastases. A controlled in vivo resorbabilityof the chemically crosslinked collagen sponge is essential to healingwithout excessive inflammation or dehiscence. The enzymatic degradationtest using collagenase from Clostridium histolicum described in detailbelow gives an excellent prediction of the in vivo resorbability.

In that test, for all samples of the sterile resilient resorbablechemically crosslinked collagen sponge according to the invention thatin vivo showed interesting volume retention and healing without adverseadvents such as excessive inflammation or dehiscence, the collagen wascompletely degraded in 3 to 5 hours. The above resilient resorbablechemically crosslinked collagen sponge is suitably prepared from tissuesof natural origin by a process comprising freeze drying and chemicalcrosslinking. Appropriate tissues of natural origin include porcine orbovine peritoneum or pericardium membranes, porcine or bovine placentamembrane and porcine or bovine SIS or dermis. Preferably the tissues ofnatural origin include porcine or bovine peritoneum membrane and porcinedermis. The above process comprising freeze drying and chemicalcrosslinking is generally followed by a sterilization step, which issuitably γ irradiation or X-ray sterilization.

The chemical crosslinking may be performed using any pharmaceuticallyacceptable crosslinking agent capable of giving to the resilientresorbable chemically crosslinked collagen sponge the required thicknessretention in respect to the initial thickness or hysteresis retention inrespect to the first loading in the cyclic compression test. Suitablesuch crosslinking agents include gluteraldehyde, formaldehyde,acetaldehyde, 1,4-butane diglycidyl ether (BDDGE),N-sulfosuccinimidyl-6-(4′-azido-2′-nitrophenylamino) hexanoate,hexamethylene diisocyanate (HMDC), cynamide, diphenylphosphorylazide,genipin, EDC (1-ethyl-3-(3-dimethylaminopropyl)-carbodiimide) and amixture of EDC and NHS (N-hydoxysuccinimide). Small amounts or traces ofthe unreacted crosslinking agent or typical direct reaction productsthereof can usually be detected in the resilient resorbable chemicallycrosslinked collagen sponge.

Preferably the chemical crosslinking is performed using a crosslinkingagent selected from gluteraldehyde, EDC(1-ethyl-3-(3-dimethylaminopropyl)-carbodiimide) and a mixture of EDCand NHS (N-hydoxysuccinimide). Interesting prototypes of resilientresorbable chemically crosslinked collagen sponges according to theinvention have indeed been prepared using each of those crosslinkingagents.

More than 1000 different prototypes of collagen sponges have beenprepared using as a crosslinking agent EDC or a mixture of EDC and NHSand tested in various in vitro tests and/or in vivo animal tests notablyin mice, rats, rabbits and dogs. Preferably the chemical crosslinking isperformed using one of those two crosslinking agents.

The resilient resorbable collagen sponge of the invention has beennotably tested in:

-   -   an animal study involving measurement of mucosa volume gain by        implantation into chronic defects of mandibles of dogs in        comparison with the gold standard SCTG (Subepithelial Connective        Tissue Graft), and    -   a clinical study to investigate its performance and safety in        tissue augmentation procedures to gain mucosal thickness around        dental implants in the oral cavity in comparison with the gold        standard for soft tissue volume augmentation SCTG (Subepithelial        Connective Tissue Graft).

In both of those studies the resilient resorbable chemically crosslinkedcollagen sponge of the invention showed after 3-month-implantation anexcellent integration into the surrounding tissues without excessiveinflammation or dehiscence, the same safety and the same (i.e. notstatistically different) soft tissue volume retention as SCTG.

The above resilient resorbable chemically crosslinked collagen spongemay be prepared by a process comprising the steps of:

-   -   (a) Submitting a porcine or bovine peritoneum or pericardium        membrane to a basic treatment in a sodium hydroxide solution at        a pH above 12, an acid treatment in a hydrochloric solution of        pH of 1 to 3, a dehydrating treatment with a water soluble        organic solvent and a degreasing treatment with an organic        solvent,        -   milling the dry membrane obtained with a cutting mill,            sieving through a 0.5-2 mm sieve and suspending the powder            obtained in an acidified water solution of pH from 2.5 to            3.5, such as to obtain a slurry of collagen fibres,    -   (b) Submitting grinded bovine or porcine dermis to a dehydrating        treatment with a water soluble organic solvent, a degreasing        treatment with an organic solvent, a basic treatment in a strong        inorganic base at a pH above 12, an acid treatment in a strong        inorganic acid at a pH from 0 to 1, rinsing with water and        suspending the collagen fibres, freeze-drying, cleaning the        dried collagen fibres with an organic solvent and grinding the        cleaned dried fibres in an acidified solution of pH from 3 to 4,        such as to obtain a slurry of collagen fibres,    -   (c) Mixing 3.5 to 4.5 parts of the slurry of collagen fibres        obtained in (a) with 0.5 to 1.5 parts of the slurry of collagen        fibres obtained in (b), such as to obtain a resulting slurry,    -   (d) Freeze-drying the resulting slurry obtained in (c) and        crosslinking the freeze-dried product in a solution containing a        crosslinking agent, washing with water and freeze-drying, and    -   (e) Optionally sterilizing the freeze-dried product obtained        in (d) by γ irradiation or X-ray irradiation.

Step (a) may be performed similarly to the process described in“Example” of EP-B1-1676592 by submitting the peritoneal membranes fromyoung calves or young pigs to washing with water, a basic treatment with2% sodium hydroxide solution, washing with water, an acid treatment in a0.5% hydrochloric solution, washing with water until a pH of 3.5 isobtained, shrinking the material with 7% saline solution, washing withwater, dehydrating with acetone and degreasing with n-hexane, millingthe dry membrane obtained with a cutting mill, sieving through a 0.5-2mm sieve and suspending the powder obtained in an acidified watersolution of pH from 2.5 to 3.5, such as to obtain a slurry of porcine orbovine peritoneum collagen fibres.

Step (a) is conveniently performed by milling the sterile membraneGeistlich Bio-Gide® (obtainable from Geistlich Pharma A.G., Switzerland)with a cutting mill, sieving through a 0.5-2 mm sieve and suspending thepowder obtained in an acidified water solution of pH from 2.5 to 3.5,such as to obtain a slurry of porcine peritoneum collagen fibres.

Preferably the powder obtained after milling with a cutting mill issieved through a 0.5-1 mm sieve.

Step (b) may be performed similarly to the process disclosed in Example7 of WO 2012/084214 by submitting grinded porcine rinds to a dehydratingtreatment with a water soluble organic solvent such as an alcohol or aketone, a degreasing treatment with an organic solvent such adichloroethane or methylene chloride, a basic treatment in a stronginorganic base at a pH above 12 for a period of 6 to 24 hours, an acidtreatment in a strong inorganic acid at a pH from 0 to 1 for a period of1 to 12 hours, rinsing with water and suspending the collagen fibres inthe presence of a swelling regulator, freeze-drying, cleaning the driedcollagen fibres with different organic solvents such as alcohols,ethers, ketones and chlorinated hydrocarbons and grinding in a colloidmill the cleaned dried fibres in an acidified solution of pH from 3 to4, such as to obtain a slurry of porcine dermis collagen fibres.

The (w/w) % collagen in the slurry of collagen fibres prepared in step(a) and (w/w) % collagen in the slurry of collagen fibres prepared instep (b) play a role in setting the density in dry state of theresilient resorbable chemically crosslinked collagen sponge. Indeed, thelatter mainly depends on one side on the (w/w) % collagen of theresulting slurry of collagen fibres obtained in step (c) by mixing 1.5to 4.5 parts of the slurry of collagen fibres obtained in (a) with 0.5to 1.5 parts of the slurry of collagen fibres obtained in (b) and on theother side on the conditions of the crosslinking reaction in step (d).

To achieve for the resilient resorbable chemically cross-linked collagensponge the required density in dry state of 50 to 65 mg/cm³, the slurryof collagen fibres prepared in step (a) contains generally from 2.0 to4.5, preferably 2.5 to 3.75 (w/w) % collagen and the slurry of collagenfibres prepared in step (b) contains generally from 3.0 to 7.0,preferably 4.0 to 6.0 (w/w) % collagen.

Step (c) comprises mixing 3.5 to 4.5 weight parts of the slurry ofcollagen fibres obtained in (a) with 0.5 to 1.5 weight parts of theslurry of collagen fibres obtained in (b), such as to obtain a resultingslurry.

This mixing step of appropriate proportions of two different slurries ofcollagen fibres coming from different porcine or bovine tissues andhaving been subjected to different treatments including differentgrinding procedures (using a cutting mill for step (a) and a colloidmill for step (b)) giving collagen fibre particles of different sizes,is a convenient method for attaining the desired porosity distributionor spectrum of the resilient resorbable chemically crosslinked collagensponge, namely interconnected pores with a median pore diameter between50 and 90 μm and at least 80%, preferably at least 90% porosity with apore diameter more than 10 μm as determined by mercury intrusionporosimetry.

The resulting slurry generally contains 3.0 to 6.5 (w/w) %, preferably3.5 to 6.0 (w/w) % collagen.

Step (d) comprises freeze-drying the resulting slurry obtained in (c),crosslinking the freeze-dried product in a solution containing acrosslinking agent, washing with water and freeze-drying.

Freeze-drying before and after the crosslinking step is generallyperformed at a temperature below −10° C.

The crosslinking agent is suitably selected from the group consisting ofgluteraldehyde, EDC (1-ethyl-3-(3-dimethylaminopropyl)-carbodiimide) anda mixture of EDC and NHS (N-hydoxysuccinimide). Other crosslinkingagents known for crosslinking collagen such as formaldehyde,acetaldehyde, 1,4-butane diglycidyl ether (BDDGE),N-sulfosuccinimidyl-6-(4′-azido-2′-nitrophenylamino) hexanoate,hexamethylene diisocyanate (HMDC), cynamide, diphenylphosphorylazide orgenipin may also be used.

When the crosslinking agent is gluteraldehyde, the sponge obtained afterfreeze-drying is suitably chemically cross-linked in a phosphate buffersolution of pH 7.0 to 7.5 containing 0.01 to 0.10%, preferably 0.04 to0.06% gluteraldehyde. The chemically crosslinked sponge may besuccessively washed with water, 1-3 M NaCl solution, 0.05-0.15 M Na₂HPO₄solution and water, before being freeze-dried.

When the crosslinking agent is EDC, the sponge obtained afterfreeze-drying is suitably first submitted to a dehydrothermal treatmentat a temperature above 110° C., then chemically crosslinked in a buffersolution containing 0.05-0.15 M MES (2-(N-morpholino)-ethanesulfonicacid) or 0.05-0.15 M acetic acid and 2-20% (w/w) of an alcohol selectedfrom the group consisting of methanol, ethanol, n-propanol, isopropanoland butanol, with 0.03-0.80, preferably 0.2-0.4 g EDC per g collagen,for a period of 1 to 8 hours. The (w/w) ratio of collagen to thereaction medium (the above buffer solution) is generally from 1/10 to1/100, preferably from 1/20 to 1/50. When the alcohol is ethanol, it issuitably present at 3-7% (w/w) in the buffer solution. The chemicallycrosslinked collagen sponge may be washed first with 0.05-0.15 M Na₂HPO₄solution, a 0.5-3 M NaCl solution, then with water before beingfreeze-dried.

When the crosslinking agent is a mixture of EDC and NHS, the spongeobtained after freeze-drying is suitably chemically crosslinked in abuffer solution containing 0.1-0.3 M MES(2-(N-morpholino)-ethanesulfonic acid) or 0.1-0.3 M acetic acid and10-70% (w/w) alcohol selected from the group consisting of methanol,ethanol, n-propanol, isopropanol and butanol, with 0.01-0.60, preferably0.05-0.2 g EDC and 0.01-0.6, preferably 0.05-0.2 g NHS, per g collagen,for a period of 1 to 8 hours. The molar ratio of EDC to NHS is generallyfrom 4 to 0.5, preferably from 2 to 1. The (w/w) ratio of collagen tothe reaction medium (the above buffer solution) is generally from 1/10to 1/100, preferably from 1/20 to 1/50. When the alcohol is ethanol, itis suitably present at 40-60% (w/w) in the buffer solution. Thechemically crosslinked collagen sponge may be washed first with0.05-0.15 M Na₂HPO₄ solution, then with water before being freeze-dried.

For each mixture of slurries of collagen fibres obtained in (c) theskilled person will be in a position based on the teaching of thepresent application, using only common general knowledge of the art androutine experimentation, to find the crosslinking agent and thecrosslinking conditions such as to obtain a resilient resorbablechemically cross-linked collagen sponge according to the inventionhaving the specified onset temperature and density in dry state.

The following has thus e.g. been found by routine experimentation forcollagen slurries containing 3.0 to 6.5 (w/w) % collagen:

-   -   When the crosslinking agent is EDC:        -   the onset temperature is increased, for a rise of the            concentration of EDC in the buffer solution, the ratio of            EDC to collagen, the (w/w) ratio of the reaction medium to            collagen or the % of alcohol in the buffer solution.        -   the density in dry state is decreased (more shrinkage of            collagen) for a rise of the % of alcohol in the buffer            solution.    -   When the crosslinking agent is a mixture EDC and NHS:        -   the onset temperature is increased, for a rise in the            concentration of the crosslinking agent in the buffer            solution, the (w/w) ratio of the crosslinking agent            (EDC+NHS) to collagen, ratio of EDC to NHS, the (w/w) ratio            of the reaction medium to collagen or the % of alcohol in            the buffer solution.        -   the density in dry state is decreased (more shrinkage of            collagen) for a rise of the % of alcohol in the buffer            solution.

The freeze-dried resilient resorbable chemically cross-linked collagensponge obtained at the end of step (d) will generally be submitted tostep (e) of sterilization by γ irradiation or X-ray irradiation. Thatstep may not be necessary if the mixture of collagen slurries obtainedin step (c) is already aseptic and step (d) is performed under asepticconditions.

The in vitro cyclic compression test and enzymatic degradation testusing collagenase from Clostridium histolyticum, which are described indetail below, are very useful in predicting the in vivo behaviour of thechemically cross-linked sponge after implantation into the oral cavity,notably its capacity of keeping volume and healing without adverseevents such as excessive inflammation or dehiscence.

The invention also relates to the above process for preparing theresilient resorbable chemically crosslinked collagen sponge.

The invention also concerns the above resilient resorbable chemicallycrosslinked collagen sponge for use as an implant for the oral cavity,the use of that resilient resorbable chemically crosslinked collagensponge for preparing an implant for the oral cavity and a method ofaugmenting soft tissue volume in the oral region, notably by fosteringthe ingrowth of gingival cells while keeping volume under mechanicalstresses, which comprises implanting into the oral cavity the aboveresilient resorbable chemically cross-linked collagen sponge.

The following experimental methods, tests and Examples illustrate theinvention without restricting its scope.

Test for Determination of the Density of the Resilient ResorbableChemically Crosslinked Collagen Sponge in Dry State

The resilient resorbable chemically crosslinked collagen sponge sampleswere introduced into tared plastic tubes which are dried in afreeze-drier for at least 2 hours at a temperature of 20° C. and apressure below 0.5 mbar. The tubes with dried samples were weighed andthe net weights of the samples in dry state calculated.

The length, width and height of the resilient resorbable chemicallycrosslinked collagen sponge samples were measured by using an electricalslide gauge, by applying enough contact pressure such that the samplesare loosely fixed (i.e. fixed to resist the force caused by their weightbut apt to move when is force is increased about 10-fold). The volumesof the samples in dry state were calculated. The density of theresilient resorbable chemically crosslinked collagen sponge in dry state(weight over volume) was then calculated for each sample.

Cyclic Compression Test

The % of initial thickness and hysteresis in respect to the firstloading after 49 cycles of compression to a pressure of 12.1 kPa weremeasured using a mechanical compression machine, namely Z2.5 materialcompression machine manufactured by Zwick Roell, using the program TestExpert II.

The measurements were performed submerged in PBS at 37° C. on sterile,resilient resorbable chemically crosslinked collagen sponge sampleswhich had been incubated for 2 hours at 37° C. in a PBS solution of pH7.4 (prepared by dissolving 80.0 g NaCl, 2.0 g KCl, 17.7 g Na₂HPO₄ and2.4 g KH₂PO₄ in 1000 ml water, diluting ten times the solution in waterand adjusting the pH with HCl to 7.4).

Samples were subjected to a total of 49 cycles of loading between 0.5and 12.1 kPa at a strain rate of 33% of initial height per min, analysisstarting at a pre-pressure of 0.25 kPa.

The initial height at 0.5 kPa pressure was used to calculate theretention of initial height after 49 cycles of loading and unloading.The “hysteresis in respect to the first loading” is the percentage workwhich was dissipated during unloading using the work (W_(1,loading) inNm) between 0.5 and 12.1 kPa of the first loading and the work from the49^(th) unloading cycle (W_(49,unloading) in Nm) according equation XY:

$\begin{matrix}{{{``\text{Hysteresis~~in~~respect~~to~~the~~first~~loading}"}\mspace{14mu}\lbrack\%\rbrack} = \frac{100*\left( {W_{1,{loading}} - W_{49,{unloading}}} \right)}{W_{1,{loading}}}} & {{Eq}\mspace{14mu}{XY}}\end{matrix}$

The program Test Expert or Excel calculates the % of retention ofinitial thickness and the % of retention of initial hysteresis after 49cycles of compression to a pressure of 12.1 kPa.

The FIGURE shows the typical result of a cyclic compression test.

For samples of the resilient resorbable chemically cross-linked collagensponge according to the invention that in vivo showed interesting volumeretention and healing without excessive inflammation or dehiscence:

-   -   the height or thickness retention in respect of the initial        height was at least 70%, preferably at least 80%, more        preferably at least 85%, after 49 cycles of compression to 12.1        kPa, and    -   the hysteresis retention in respect to the first loading after        49 cycles of compression to 12.1 kPa was less than 55%,        preferably less than 45%.        Enzymatic Degradation Test Using Collagenase from Clostridium        histolyticum

In the human body collagens are degraded by human tissuematrix-metalloproteinase (MMP), cathepsins and putatively by some serineproteinases. Best studied are the MMPs where collagenases (notablyMMP-1, MMP-8, MMP-13 and MMP-18) are the most important enzymes fordirect collagen degradation (Lauer-Fields et al. 2002 Matrixmetalloproteinases and collagen catabolism in Biopolymers—PeptideScience Section and Song et al. 2006 Matrix metalloproteinase dependentand independent collagen degradation in Frontiers in Bioscience).

Collagenase capability to degrade collagen tissues and membranes dependson the substrate flexibility and collagen type, MMP active sites and MMPexosites.

Collagenases align at the triple helical collagen, unwind it andsubsequently cleave it (Song et al. 2006, see above).

With the view of overcoming differences in degradation between thedifferent collagen types, collagenase degradation of collagen is oftenassessed using collagenase from Clostridium histolyticum which has ahigh catalytic speed (Kadler et al. 2007 Collagen at a glance in J CellSci). Generally, a natural collagen product degrades faster than achemically cross-linked collagen product.

In this test the collagen products (samples of resilient resorbablechemically crosslinked collagen sponge according to the invention wereincubated at 37° C. with 50 units/ml from Clostridium histolyticum (oneunit being defined as liberating peptides from collagen from bovineAchilles tendon equivalent in ninhydrin color to 1.0 micromole ofleucine in 5 hours at pH 7.4 at 37° C. in the presence of calcium ions)in a calcium containing Tris-buffer and the degradation of the collagenmatrix was measured visually and with the “DC Protein Assay” fromBio-Rad Laboratories (Hercules, USA, Order Nr. 500-0116) using CollagenType I as reference material. The collagen concentration was determinedusing a microwellplate spectrometer (Infinite M200, available fromTecan).

For samples of the resilient resorbable chemically cross-linked collagensponge according to the invention that in vivo showed healing withoutexcessive inflammation or dehiscence, the collagen was completelydegraded (no collagen fibre detectable by visual inspection) within 3 to5 hours.

EXAMPLE 1 Preparation of a Slurry of Collagen Fibres Derived fromPorcine Peritoneum

The peritoneal membranes from young pigs were completely freed fromflesh and grease by mechanical means, washed under running water andtreated with 2% NaOH solution for 12 hours. The membranes were thenwashed under running water and acidified with 0.5% HCl. After thematerial had been acidified through its entire thickness (about 15 min)the material was washed until a pH of 3.5 was obtained. The material wasthen shrunk with 7% saline solution, neutralised with 1% NaHCO₃ solutionand washed under running water. The material was then dehydrated withacetone and degreased with n-hexane.

The material was dried using ethanol ether and milled with a cuttingmill (e.g. Pulverisette 25 from Fritsch: seefetsch.de./produkte/mahlen/schneidmuehlen/pulverisette-25 or SM300 fromRetsch: retsch.de/de/produkte/zerkleinern/schneidmuehlen) which includesa trapezoidal sieve of 0.5 to 1.0 mm.

A 4% (w/w) slurry of collagen fibres and a 6% (w/w) slurry of collagenfibres were prepared by suspending adequate amounts of the dried powderin water and adjusting the pH to 2.6 with 10 mM hydrochloric acid.

EXAMPLE 2 Preparation of a Slurry of Collagen Fibres Derived from aSterile Geistlich Bio-Gide® Membrane

A Geistlich Bio-Gide® membrane (available from Geistlich Pharma AG,CH-6110, Switzerland) was dried and milled with a cutting mill whichincludes a trapezoidal sieve of 0.5 to 1.0 mm. A 4% (w/w) collagenslurry of collagen fibres and a 6% (w/w) collagen slurry of collagenfibres were prepared by suspending adequate amounts of the dried powderin water and adjusting the pH to 2.6 with 10 mM hydrochloric acid.

EXAMPLE 3 Preparation of a Slurry of Collagen Fibres Derived from PigDermis

Porcine hides were ground in a meat grinder to pieces of 1 to 20 mm. Thewater was removed using a water soluble solvent such as an alcohol or aketone. The collagen fibres were defatted using a chlorinatedhydrocarbon such as dichloroethane or methylene chloride or anon-chlorinated hydrocarbon such as hexane or toluene. After removingthe solvent the collagen was treated with a strong inorganic base at apH above 12 for a period of 6 to 24 hours and treated with a stronginorganic acid at a pH of 0 to 1 for a period of 1 to 12 hours. Theexcess acid was removed by rinsing with water and the suspension washomogenized by colloid milling to a 0.5 to 2% homogenous suspension ofcollagen fibres in the presence of a swelling regulator such as aninorganic salt. The suspension was dried by freeze-drying and the drycollagen fibres were successively cleaned with different organicsolvents such as alcohols, ethers, ketones and chlorinated hydrocarbons,the solvents being then evaporated under vacuum to a solvent residue ofless than 1% (w/w).

A 2.5% (w/w) collagen slurry of collagen fibres and a 3.75% (w/w)collagen slurry of collagen fibres were prepared by finely grinding bycolloid milling adequate amounts of the cleaned dry fibres obtainedabove with water at a pH of 3.4.

EXAMPLE 4 Preparation of a Resilient Resorbable Collagen SpongeChemically Crosslinked with EDC

4 parts of the 4% (w/w) collagen slurry of collagen fibres obtained inExample 1 or Example 2 were mixed with 1 part of the 2.5% (w/w) collagenslurry of collagen fibres obtained in Example 3 and poured into molds of8×25×25 mm. The resulting 3.7% slurry of collagen fibres was dried byfreeze-drying at −45° C.

The dried collagen sponges were then dehydrothermally treated at 120° C.for 24 hours under reduced pressure (less than 200 mbar).

The collagen sponges were then chemically crosslinked in a buffersolution containing 0.1 M MES (2-(N-morpholino)-ethanesulfonic acid) and5% ethanol at a pH of 5.5 with 0.3 g EDC(1-ethyl-3-(3-dimethylaminopropyl)carbodiimide) per g collagen, underagitation at room temperature for a period of 120 min.

The chemically crosslinked collagen sponges were washed first with 0.10M Na2HPO4 solution, 1M NaCl solution, 2M NaCl solution, then with waterand freeze-dried at −45° C.

The dried chemically crosslinked collagen sponges were gamma-sterilizedat 30 kGy. The measured onset temperature and density in dry state ofthe sterilized chemically crosslinked collagen sponges were 47° C. and64 mg/cm³, respectively.

After 49 cycles of compression to a pressure of 12.1 kPa in PBS at 37°C., the sterilized chemically crosslinked collagen sponges showed aretention of 87% of its initial thickness and 41% of the initialhysteresis.

Mercury intrusion porosimetry showed for the sterilized chemicallycrosslinked collagen sponges a median pore diameter of 88 μm and 95%porosity with a pore diameter more than 10 μm.

The enzymatic degradation test using collagenase from Clostridiumhistolyticum showed a complete degradation of collagen within 3.25hours.

EXAMPLE 5 Preparation of a Resilient Resorbable Collagen SpongeChemically Crosslinked with a Mixture of EDC and NHS

Four parts of the 6% (w/w) slurry of collagen fibres obtained in Example1 or Example 2 were mixed with one part of the 3.75% (w/w) slurry ofcollagen fibres obtained in Example 3 and poured into molds of a heightof 6 mm. The resulting 5.55% (w/w) collagen slurry of collagen fibreswas dried by freeze drying at −10° C. These sponges were chemicallycrosslinked in a solution containing 0.2 M MES(2-(N-morpholino)-ethanesulfonic acid) and 50% w/w ethanol at a pH of5.5 with 0.1 g EDC (1-ethyl-3-(3-dimethylaminopropyl)-carbodiimide) pergram collagen and 0.1 g NHS (N-hydoxysuccinimide) per gram collagen,under agitation at room temperature for a period of 120 min. Thechemically crosslinked sponges were washed first with 0.1 M Na₂HPO₄solution, 1M NaCl solution, 2M NaCl solution, then with water and freezedried at −10° C.

The dried chemically crosslinked collagen sponges were sterilized byγ-irradiation at 26 kGy.

The measured onset temperature and density in dry state of thesterilized chemically crosslinked collagen sponges were 52° C. and 59mg/cm³, respectively. After 49 cycles of compression to a pressure of12.1 kPa in PBS at 37° C., the sterilized chemically crosslinkedcollagen sponges showed a retention of 90% of its initial thickness and38% of the hysteresis in respect of the first loading. Mercury intrusionporosimetry showed for the sterilized chemically cross-linked collagensponges a median pore diameter of 69.1 μm and 93.1% porosity with a porediameter more than 10 μm.

The enzymatic degradation test using collagenase from Clostridiumhistolyticum showed a complete degradation of collagen within 3.5 hours.

EXAMPLE 6 Preparation of a Resilient Resorbable Collagen SpongeChemically Crosslinked with a Mixture of EDC and NHS (without aSterilization Step)

Four parts of the 6% (w/w) slurry of collagen fibres obtained in Example2 were mixed with one part of the 3.75% (w/w) slurry of collagen fibresobtained in Example 3 and poured into molds of a height of 6 mm. Theresulting 5.55% (w/w) collagen slurry of collagen fibres was dried byfreeze drying at −10° C.

These sponges were chemically crosslinked in a solution containing 0.2 MMES (2-(N-morpholino)-ethanesulfonic acid) and 50% w/w ethanol at a pHof 5.5 with 0.01 g EDC (1-ethyl-3-(3-dimethylaminopropyl)-carbodiimide)per gram collagen and 0.01 g NHS (N-hydoxysuccinimide) per gramcollagen, under agitation at room temperature for a period of 120 min.The chemically crosslinked sponges were washed first with 0.1 M Na₂HPO₄solution, 1M NaCl solution, 2M NaCl solution, then with water and freezedried at −10° C.

The measured onset temperature and density in dry state of thechemically crosslinked collagen sponges were 57° C. and 57 mg/cm³respectively.

After 49 cycles of compression to a pressure of 12.1 kPa in PBS at 37°C., the chemically crosslinked collagen sponges showed a retention of80% of its initial thickness.

Mercury intrusion porosimetry showed for the chemically crosslinkedcollagen sponges a median pore diameter of 71.0 μm and 94.0% porositywith a pore diameter more than 10 μm.

EXAMPLE 7 Preparation of a Resilient Resorbable Collagen SpongeChemically Crosslinked with Glutaraldehyde

Four parts of the slurry of collagen fibres obtained in Example 1 weremixed with one part of the slurry of collagen fibres obtained in Example3 and poured into molds of a height of 6 mm. The collagen slurry wasdried by freeze drying at minus 45° C. These sponges were chemicallycrosslinked in a sodium phosphate buffer (pH 7.0-7.5) containing 0.05%(w/w) glutaraldehyde at 10° C. for 60 min. The chemically crosslinkedcollagen sponges were successively washed with water, 2 M NaCl solutionand 0.1 M Na₂HPO₄ solution. After the final rinse with water the spongeswere freeze dried at −45° C.

The chemically crosslinked collagen sponges were sterilized byγ-irradiation at 25 kGy.

The measured onset temperature and density in dry state of thesterilized chemically crosslinked collagen sponges were respectively 51°C. and 52 mg/cm³.

After 49 cycles of compression to a pressure of 12.1 kPa at 37° C., thesterilized chemically crosslinked collagen sponges in PBS showed aretention of 74% of their initial thickness and 48% hysteresis inrespect of the first loading.

Mercury intrusion porosimetry showed for the sterilized chemicallycrosslinked collagen sponges a median pore diameter of 63.7 μm and 92.7%porosity with a pore diameter more than 10 μm.

The enzymatic degradation test using collagenase from Clostridiumhistolyticum showed a complete degradation of collagen within 4.5 hours.

The invention claimed is:
 1. A resilient resorbable chemicallycrosslinked collagen sponge for promoting soft tissue volumeaugmentation in an oral cavity, comprising 60-96% (w/w) collagen and4-40% (w/w) elastin, which shows by mercury intrusion porosimetryinterconnected pores with a median pore diameter between 50 and 90 μmand at least 80% porosity with a pore diameter more than 10 μm, an onsettemperature of 45 to 57° C. and a density in dry state from 50 to 65mg/cm³.
 2. The resilient resorbable chemically crosslinked collagensponge of claim 1 which shows an onset temperature from 46 to 53° C. 3.The resilient resorbable chemically crosslinked collagen sponge of claim1, which shows a density in dry state from 50 to 60 mg/cm³.
 4. Theresilient resorbable chemically crosslinked collagen sponge of claim 1,which comprises 70-90% (w/w) collagen and 10-30% (w/w) elastin.
 5. Theresilient resorbable chemically crosslinked collagen sponge of claim 1,which shows at least 90% porosity with a pore diameter more than 10 μm.6. The resilient resorbable chemically crosslinked collagen sponge ofclaim 1, which was obtained using a cross-linking agent selected fromthe group consisting of gluteraldehyde, EDC(1-ethyl-3-(3-dimethylaminopropyl)-carbodiimide) and a mixture of EDCand NHS (N-hydoxysuccinimide).
 7. The resilient resorbable chemicallycrosslinked collagen sponge of claim 1, which was derived from tissuesof natural origin by a process comprising freeze drying and chemicalcrosslinking, optionally followed by γ-sterilization or X-raysterilization.
 8. The resilient resorbable chemically crosslinkedcollagen sponge of claim 7, wherein the tissues of natural origininclude porcine or bovine peritoneum or pericardium membranes, porcineor bovine placenta membrane, or porcine or bovine SIS or dermis.
 9. Theresilient resorbable chemically crosslinked collagen sponge of claim 1,which wetted by a PBS solution retains at least 70% of initial thicknessafter 49 cycles of compression to a pressure of 12.1 kPa.
 10. Theresilient resorbable chemically crosslinked collagen sponge of claim 1,which wetted by a PBS solution retains less than 55% hysteresis withrespect to the first loading after 49 cycles of compression to apressure of 12.1 kPa.
 11. The resilient resorbable chemicallycrosslinked collagen sponge of claim 1, which shows after implantationin the oral cavity the same volume retention as SCTG (SubepithelialConnective Tissue Graft).
 12. A process for making the resilientresorbable chemically crosslinked collagen sponge of claim 1, whichcomprises the following steps: (a) submitting a porcine or bovineperitoneum or pericardium membrane to a basic treatment in a sodiumhydroxide solution at a pH above 12, an acid treatment in a hydrochloricsolution of pH of 1 to 3, a dehydrating treatment with a water solubleorganic solvent and a degreasing treatment with an organic solvent,milling the dry membrane obtained with a cutting mill, sieving through a0.5-2 mm sieve and suspending the powder obtained in an acidified watersolution of pH from 2.5 to 3.5, such as to obtain a first slurry ofcollagen fibres, (b) separately from step (a) submitting grinded bovineor porcine dermis to a dehydrating treatment with a water solubleorganic solvent, a degreasing treatment with an organic solvent, a basictreatment in a strong inorganic base at a pH above 12, an acid treatmentin a strong inorganic acid at a pH from 0 to 1, rinsing with water andsuspending the collagen fibres, freeze-drying, cleaning the driedcollagen fibres with an organic solvent and grinding the cleaned driedfibres in an acidified solution of pH from 3 to 4, such as to obtain asecond slurry of collagen fibres, (c) mixing 3.5 to 4.5 parts of thecollagen fibres slurry obtained in (a) with 0.5 to 1.5 parts of thecollagen fibres slurry obtained in (b), such as to obtain a resultingslurry, (d) freeze-drying the resulting slurry obtained in (c) to obtaina first freeze-dried product, and crosslinking the first freeze-driedproduct in a solution containing a crosslinking agent, washing withwater and freeze-drying to obtain a second freeze-dried product, and (e)optionally sterilizing the second freeze-dried product obtained in (d)by γ irradiation or X-ray irradiation.
 13. The process according toclaim 12, wherein the crosslinking agent is selected from the groupconsisting of gluteraldehyde, EDC(1-ethyl-3-(3-dimethylaminopropyl)-carbodiimide) and a mixture of EDCand NHS (N-hydoxysuccinimide).
 14. The process according to claim 12,wherein the slurry of collagen fibres prepared in step (a) contains 2.5to 3.75 (w/w) % collagen and the slurry of collagen fibres prepared instep (b) contains from 4.0 to 6.0 (w/w) % collagen.
 15. A method ofpromoting soft tissue volume augmentation in an oral cavity of a subjectin need thereof, comprising implanting the resilient resorbablechemically cross-linked collagen sponge of claim 1 into said subject'soral cavity to promote tissue volume augmentation.
 16. An implantcomprising a sterile resilient resorbable chemically crosslinkedcollagen sponge that is resistant to cyclic compression, comprising60-96% (w/w) collagen and 4-40% (w/w) elastin, which shows by mercuryintrusion porosimetry interconnected pores with a median pore diameterbetween 50 and 90 μm and at least 80% porosity with a pore diameter morethan 10 μm, an onset temperature of 45 to 57° C. and a density in drystate from 50 to 65 mg/cm³.
 17. The implant of claim 16, wherein thesterile resilient resorbable chemically crosslinked collagen sponge hasan onset temperature from 46 to 53° C.
 18. The implant of claim 16,wherein the sterile resilient resorbable chemically crosslinked collagensponge has a density in dry state from 50 to 60 mg/cm³.
 19. The implantof claim 16, wherein the sterile resilient resorbable chemicallycrosslinked collagen sponge comprises 70-90% (w/w) collagen and 10-30%(w/w) elastin.
 20. The implant of claim 16, wherein the sterileresilient resorbable chemically crosslinked collagen sponge has at least90% porosity with a pore diameter more than 10 μm.
 21. The implant ofclaim 16, wherein the sterile resilient resorbable chemicallycrosslinked collagen was obtained using a crosslinking agent selectedfrom the group consisting of gluteraldehyde, EDC(1-ethyl-3-(3-dimethylaminopropyl)-carbodiimide) and a mixture of EDCand NHS (N-hydoxysuccinimide).
 22. The implant of claim 16, wherein thesterile resilient resorbable chemically crosslinked collagen sponge wasderived from tissues of natural origin by a process comprising freezedrying and chemical crosslinking, optionally followed by γ-sterilizationor X-ray sterilization.
 23. The implant of claim 22, wherein the tissuesof natural origin include porcine or bovine peritoneum or pericardiummembranes, porcine or bovine placenta membrane, or porcine or bovine SISor dermis.
 24. The implant of claim 16, when wetted by a PBS solutionretains at least 70% of initial thickness after 49 cycles of compressionto a pressure of 12.1 kPa.
 25. The implant of claim 16, when wetted by aPBS solution retains less than 55% hysteresis with respect to the firstloading after 49 cycles of compression to a pressure of 12.1 kPa. 26.The implant of claim 16, having properties such that the collagencompletely degrades within 3 to 5 hours in an enzymatic degradation testusing collagenase from Clostridium histolyticum.
 27. The implant ofclaim 16, wherein the sterile resilient resorbable chemicallycrosslinked collagen sponge comprises 70-90% (w/w) collagen and 10-30%(w/w) elastin, which shows by mercury intrusion porosimetryinterconnected pores with a median pore diameter between 50 and 90 μmand at least 90% porosity with a pore diameter more than 10 μm, an onsettemperature of 46 to 53° C. and a density in dry state from 50 to 60mg/cm³.